US10945691B2 - Sensitivity optimized patient positioning system for dark-field x-ray imaging - Google Patents

Sensitivity optimized patient positioning system for dark-field x-ray imaging Download PDF

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US10945691B2
US10945691B2 US16/497,066 US201816497066A US10945691B2 US 10945691 B2 US10945691 B2 US 10945691B2 US 201816497066 A US201816497066 A US 201816497066A US 10945691 B2 US10945691 B2 US 10945691B2
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patient
field
distance
abutting
abutting surface
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US20200015767A1 (en
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Thomas Koehler
Andriy Yaroshenko
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Koninklijke Philips NV
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Koninklijke Philips NV
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/48—Diagnostic techniques
    • A61B6/484—Diagnostic techniques involving phase contrast X-ray imaging
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/08—Auxiliary means for directing the radiation beam to a particular spot, e.g. using light beams
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4291—Arrangements for detecting radiation specially adapted for radiation diagnosis the detector being combined with a grid or grating
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/58—Testing, adjusting or calibrating thereof
    • A61B6/589—Setting distance between source unit and patient

Definitions

  • the present invention relates to a radiography system for grating based Dark-Field and/or phase-contrast X-ray imaging and a method for capturing a Dark-Field and/or phase-contrast X-ray image.
  • Standard X-ray imaging techniques rely on a decrease of the X-ray beam's intensity due to attenuation by an object when traversing the object to be irradiated, which can be measured with the assistance of an X-ray detector.
  • interferometric methods for instance by using a Talbot-Lau type interferometer with three gratings in the beam, two additional physical effects create contrast that can be used for imaging.
  • Phase-contrast X-ray imaging uses information concerning changes in the phase by refraction of an X-ray beam that passes through an object in order to create image data.
  • Dark-Field contrast X-ray imaging uses information concerning small-angle scattering. Dark-Field and/or phase-contrast X-ray imaging may take place utilizing inverse geometry. However, it has been shown that there is a trade-off between the sensitivity of the system and the field of view that is achieved.
  • a radiography system for grating based Dark-Field and/or phase-contrast X-ray imaging comprises a source unit, a detection unit and a patient support with a patient abutting surface.
  • the source unit and the detection unit are arranged along an optical axis and the patient support is arranged in between.
  • the distance between the source unit and the patient abutting surface along the optical axis is adaptable.
  • the abutting distance and an actual sensitivity, based on the abutting distance, are taken into account for imaging, such that a trade-off between sensitivity and field of view in a patient specific manner can be achieved.
  • a radiography system for grating based Dark-Field and/or phase-contrast X-ray imaging comprises a source unit, a detection unit and a patient support with a patient abutting surface.
  • the source unit and the detection unit are arranged along an optical axis and the patient support is arranged in between. The distance between the source unit and the patient abutting surface along the optical axis is adaptable.
  • the distance between the source unit and the patient abutting surface can also be referred to as abutting distance d A .
  • the technology of grating based Dark-Field and/or phase-contrast X-ray imaging requires an insertion of three gratings into the beam, or at least two when the source provides coherent X-rays.
  • the source unit comprises a first grating G 0 and a second grating G 1 , provided downstream the first grating, and the detection unit comprises a third grating G 2 .
  • the maximum sensitivity is reached when the patient is positioned at G 1 and decreases linear to 0 at G 2 .
  • the movability of the patient support unit relates to a relocating of the patient support unit.
  • the relocating can also be referred to as shifting.
  • the source unit comprises a first grating G 0 and a second grating G 1 and the detection unit comprises a third grating G 2 ;
  • the radiography system for grating based Dark-Field and/or phase-contrast X-ray imaging utilizes inverse geometry where the distance between the first grating G 0 and the second grating G 1 is smaller than the distance between the second grating G 1 and the third grating G 2 .
  • inverse geometry relates to a configuration, where the distance between G 0 and G 1 is smaller than the distance between G 1 and G 2 and where the object, i.e. the patient, is placed between the second and the third grating.
  • the radiography system for grating based Dark-Field and/or phase-contrast X-ray imaging utilizes symmetric geometry, where the distance between G 0 and G 1 is the same as the distance between G 1 and G 2 .
  • the radiography system for grating based Dark-Field and/or phase-contrast X-ray imaging utilizes so-called direct geometry, where the distance between G 0 and G 1 is larger than the distance between G 1 and G 2 .
  • the patient is placed between the first and the second grating.
  • the abutting distance d A between the source unit and the patient abutting surface along the optical axis is adaptable by moving the source unit.
  • the contact surface for the patient may have several discrete positions along the optical axis, e.g., large, medium, and small patient.
  • the radiography system for grating based Dark-Field and/or phase-contrast X-ray imaging comprises a position detection device and an image generation unit.
  • the position detection device is configured to determine an actual position of the patient abutting surface and to feed the actual position into the image generation unit, and the image generation unit uses an actual position to generate an image.
  • the generation of data for an image takes the actual sensitivity into account to generate an image.
  • the patient support is provided between the source unit and the detection unit along the optical axis such that the best trade-off between sensitivity and field of view in a patient specific manner is achieved.
  • the radiography system for grating based Dark-Field and/or phase-contrast X-ray imaging comprises an indicating unit for indicating a field of view.
  • the position detection device is configured to determine the abutting distance d A between the source unit and the patient abutting surface.
  • the position detection device comprises a stereo camera.
  • the stereo camera is configured to determine an abutting distance d A between the source unit and the patient abutting surface.
  • the stereo camera is configured to determine the size of the patient and determines an appropriate abutting distance d A between the source and the patient abutting surface.
  • the radiography system for grating based Dark-Field and/or phase-contrast X-ray imaging is configured to determine a geometric shape of the patient to be irradiated.
  • the system is also configured to determine the field of view based on the geometric shape and to determine based on the field of view the distance between the source unit and the patient abutting surface, i.e. the object to be irradiated.
  • the distance between the source unit and the patient abutting surface can also be referred to as patient distance d P , or object distance d O .
  • the stereo camera is used together with an anatomical model of a human thorax to estimate the distance of the mid-lung plane to the contact surface.
  • the system supports at least two acquisition modes, one with large field of view and low dark-field sensitivity (bottom surface close to the detector) and one with small field of view and high dark-field sensitivity (surface farther away from the detector).
  • the method comprises the following steps:
  • the step a) of adapting of the abutting distance d A between the patient abutting surface and the source unit along the optical axis comprises the following sub-steps:
  • a2) determining an actual position between the source unit and the patient abutting surface until a field of view corresponds to an area of interest, wherein the target distance d T is used to adapt the abutting distance;
  • a computer program element for controlling a radiography system for grating based Dark-Field and/or phase-contrast X-ray imaging, which, when being executed by a processing unit, is adapted to perform the method steps for capturing a Dark-Field and/or phase-contrast X-ray image.
  • the invention relates a system and a method to locate patient along an optical axis for grating based Dark Field and/or phase-contrast X-ray imaging.
  • the patient is located either next to a source unit or a detection unit.
  • An indicating unit illuminates with its cone of light the field of view.
  • the patient is moved until the field of view corresponds with the area of interest.
  • the distance d T between the source unit and the patient is taken into account to generate an image with the optimal trade-off between the sensitivity of the system and the field of view.
  • FIG. 1 shows a schematic view of a radiography system for grating based Dark-Field and/or phase-contrast X-ray imaging
  • FIG. 2 shows a schematic view of a patient arranged in radiography system in two different positions
  • FIG. 3 shows a schematic view of a field of view of a region of interest
  • FIGS. 4 a , 4 b and 4 c show the distributions of the sensitivity and the field of view along the optical axis.
  • FIG. 5 shows an example of a method for capturing a Dark-Field and/or phase-contrast X-ray image.
  • FIG. 1 shows a radiography system 10 for grating based Dark-Field and/or phase-contrast X-ray imaging.
  • the radiography system 10 for grating based Dark-Field and/or phase-contrast X-ray imaging comprises a source unit 12 , a detection unit 14 with a patient abutting surface 18 .
  • the source unit 12 and the detection unit 14 are arranged along an optical axis 13 and the patient support unit 16 with the patient abutting surface 18 is arranged in between.
  • the patient support unit is movably arranged to be temporarily fixed in at least two different positions along the optical axis 13 .
  • the radiography system 10 for grating based Dark-Field and/or phase-contrast X-ray imaging may further comprise a position detection device 20 and an image generation unit 22 .
  • the position detection device 20 is configured to determine an actual position of the patient abutting surface 18 and to feed the actual position into the image generation unit 22 , and the image generation unit 22 uses an actual position to generate an image.
  • FIG. 2 a and FIG. 2 b show two different positions of a patient standing next to the patient abutting surface 18 .
  • the distance between the patient to the detection unit 14 is smaller compared to the field of view 26 in FIG. 2 b , and therefore the field of view 26 is increased.
  • the abutting distance d A between the source unit 12 and the patient abutting surface 18 along the optical axis 13 is adaptable in a discrete manner.
  • the abutting distance d A between the source unit 12 and the patient abutting surface 18 along the optical axis 13 is separated in several discrete positions along the optical axis 13 , e.g., large, medium, and small patient.
  • the discrete positions comprise steps of 1 cm. In another example the discrete positions comprise steps of 1 cm to 5 cm.
  • the abutting distance d A between the source unit 12 and the patient abutting surface 18 along the optical axis 13 is adaptable in a continuous manner.
  • the patient abutting surface 18 for the patient is moved continuously along the optical axis 13 between a minimum and maximum position.
  • FIG. 3 shows a field of view 26 of a chest of a patient.
  • the field of view 26 is indicated via an indicating unit 24 .
  • the indicating unit 24 may be configured as a light visor.
  • the light visor indicates the borders of the area to be irradiated by X-ray. With its cone of light, the light visor illuminates the field of view.
  • field of view can also be referred as area to be inspected.
  • the indicating unit is a focal layer positioning beam.
  • the area to be inspected can also be referred to as an area of interest.
  • the sensitivity S of the system and a field of view of image have an interdependency in accordance with the distance d A of the source unit 12 to the patient abutting surface 18 .
  • FIG. 4 a shows the distribution of the sensitivity S along the optical axis 13 starting from grating G 0 with a sensitivity S of 0 (zero) rising on a linear basis to a maximum sensitivity at the grating G 1 . From the grating G 1 , the sensitivity S decreases on a linear basis to 0 at the grating G 2 . According to an example, the grating G 0 and the grating G 1 are united in the source unit 12 .
  • FIG. 4 b shows the distribution of the sensitivity S along the optical axis D.
  • the sensitivity S has its maximum at the radiation outlet of the source unit 12 , e.g. the X-ray window of the tube, and decreases on a linear basis to 0 at the grating G 2 arranged in the detection unit 14 .
  • FIG. 4 c shows the distribution of the field of view 26 along the optical axis D.
  • the minimum field of view 26 is just next to the source unit 12 and rises on a linear basis to a maximum just next to the detection unit 14 .
  • the system supports at least two acquisition modes, one with large field of view and low dark-field sensitivity (bottom surface close to the detector) and one with small field of view and high dark-field sensitivity (surface farther away from the detector).
  • FIG. 5 shows a method 100 for capturing a Dark-Field and/or phase-contrast X-ray image comprising the following steps:
  • abutting distance d A between the patient abutting surface and the source unit is adapted along an optical axis.
  • step 104 also referred to as step b
  • the patient abutting surface is temporary fixed.
  • step 106 the patient to be irradiated is irradiated.
  • step 108 also referred to as step d
  • a Dark-Field and/or phase-contrast X-ray image is captured.
  • a patient to be irradiated is positioned between a source unit and a patient abutting surface.
  • a target distance d T between the source unit and the object to be irradiated is determined until a field of view corresponds to an area of interest, wherein the target distance d T is used to adapt the distance.
  • a third substep 114 also referred to as step a3), the distance between the source unit and the object to be irradiated is feeded to an image generation unit, wherein the image generation unit is adapted to take an actual sensitivity S, based on the distance between the source unit and the object to be irradiated, into account to generate an image.
  • the positioning takes place in a discrete manner or a continuous manner wherein the adapting of distance is carried out via a stereo camera.
  • the distance between the patient abutting surface and the source unit is adapted until a field of view corresponds to an area of interest.
  • correlates can also be referred to as a maximum proportion of area of interest in the field of view.
  • a computer program or a computer program element is provided that is characterized by being adapted to execute the method steps of the method according to one of the preceding embodiments, on an appropriate system.
  • the computer program element might therefore be stored on a computer unit, which might also be part of an embodiment of the present invention.
  • This computing unit may be adapted to perform or induce a performing of the steps of the method described above. Moreover, it may be adapted to operate the components of the above described apparatus.
  • the computing unit can be adapted to operate automatically and/or to execute the orders of a user.
  • a computer program may be loaded into a working memory of a data processor.
  • the data processor may thus be equipped to carry out the method of the invention.
  • This exemplary embodiment of the invention covers both, a computer program that right from the beginning uses the invention and a computer program that by means of an up-date turns an existing program into a program that uses the invention.
  • the computer program element might be able to provide all necessary steps to fulfil the procedure of an exemplary embodiment of the method as described above.
  • a computer readable medium such as a CD-ROM
  • the computer readable medium has a computer program element stored on it which computer program element is described by the preceding section.
  • a computer program may be stored and/or distributed on a suitable medium, such as an optical storage medium or a solid state medium supplied together with or as part of other hardware, but may also be distributed in other forms, such as via the internet or other wired or wireless telecommunication systems.
  • a suitable medium such as an optical storage medium or a solid state medium supplied together with or as part of other hardware, but may also be distributed in other forms, such as via the internet or other wired or wireless telecommunication systems.
  • the computer program may also be presented over a network like the World Wide Web and can be downloaded into the working memory of a data processor from such a network.
  • a medium for making a computer program element available for downloading is provided, which computer program element is arranged to perform a method according to one of the previously described embodiments of the invention.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Medical Informatics (AREA)
  • Engineering & Computer Science (AREA)
  • Radiology & Medical Imaging (AREA)
  • Molecular Biology (AREA)
  • Biophysics (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Optics & Photonics (AREA)
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  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
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  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Apparatus For Radiation Diagnosis (AREA)
  • Analysing Materials By The Use Of Radiation (AREA)
US16/497,066 2017-03-24 2018-02-27 Sensitivity optimized patient positioning system for dark-field x-ray imaging Active US10945691B2 (en)

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
EP17162697 2017-03-24
EP17162697.1A EP3378397A1 (fr) 2017-03-24 2017-03-24 Système de positionnement de patient à sensibilité optimisée pour l'imagerie par rayons x en champ sombre
EP17162697.1 2017-03-24
PCT/EP2018/054849 WO2018172024A1 (fr) 2017-03-24 2018-02-27 Système de positionnement de patient à sensibilité optimisée pour imagerie par rayons x en champ sombre

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EP (2) EP3378397A1 (fr)
JP (1) JP7181215B2 (fr)
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WO (1) WO2018172024A1 (fr)

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CN111643100B (zh) * 2019-11-21 2021-10-15 清华大学 相衬成像系统信息表征方法及系统
EP4014879A1 (fr) * 2020-12-16 2022-06-22 Koninklijke Philips N.V. Visualisation de champ de vision pour systèmes d'imagerie à rayons x à contraste de phases

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WO2018172024A1 (fr) 2018-09-27
EP3378397A1 (fr) 2018-09-26
JP7181215B2 (ja) 2022-11-30
RU2019133541A (ru) 2021-04-26
JP2020513973A (ja) 2020-05-21
US20200015767A1 (en) 2020-01-16
EP3600043A1 (fr) 2020-02-05
RU2019133541A3 (fr) 2021-07-05
CN110520049A (zh) 2019-11-29
CN110520049B (zh) 2023-09-12

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